Self-locking electrode assembly usable with an implantable medical device

ABSTRACT

An electrode assembly for an implantable medical device, including a spine, and a plurality of electrodes protruding from the spine. At least two electrodes protrude from the spine in opposing directions and define a nerve-receiving channel. When the electrode assembly is not coupled to a nerve and the electrodes are in a relaxed state position, the nerve receiving channel comprises a cross-sectional area that is substantially less than a cross-sectional area of a nerve to which the electrode assembly is adapted to be coupled. And when coupled to the nerve, each electrode wraps around and directly contacts at least 60% of the circumference of the nerve.

CROSS-REFERENCES TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.10/402,911, filed on Mar. 27, 2003, which is: (i) a continuation-in-partof U.S. patent application Ser. No. 09/963,777, filed on Sep. 26, 2001,which is a continuation-in-part of U.S. patent application Ser. No.09/671,850, filed on Sep. 27, 2000, now issued as U.S. Pat. No.6,522,926; and (ii) claims the benefit of U.S. Provisional PatentApplication No. 60/368,222, filed on Mar. 27, 2002, the disclosures ofeach of the above being hereby incorporated by reference in theirentirety. The parent application for this application has incorporatedby reference the disclosures of the following U.S. patent applications:U.S. patent application Ser. No. 09/964,079, filed on Sep. 26, 2001, nowissued as U.S. Pat. No. 6,985,774, and U.S. patent application Ser. No.09/963,991, filed on Sep. 26, 2001, now issued as U.S. Pat. No.6,850,801, now issued as U.S. Pat. No. 6,850,801, the disclosures ofwhich are also effectively incorporated by reference herein.

BACKGROUND OF THE INVENTION Field of the Invention

The present invention generally relates to medical devices and methodsof use for the treatment and/or management of cardiovascular and renaldisorders. Specifically, the present invention relates to devices andmethods for controlling the baroreflex system for the treatment and/ormanagement of cardiovascular and renal disorders and their underlyingcauses and conditions.

Cardiovascular disease is a major contributor to patient illness andmortality. It also is a primary driver of health care expenditure,costing more than $326 billion each year in the United States.Hypertension, or high blood pressure, is a major cardiovascular disorderthat is estimated to affect over 50 million people in the United Satesalone. Of those with hypertension, it is reported that fewer than 30%have their blood pressure under control. Hypertension is a leading causeof heart failure and stroke. It is the primary cause of death in over42,000 patients per year and is listed as a primary or contributingcause of death in over 200,000 patients per year in the U.S.Accordingly, hypertension is a serious health problem demandingsignificant research and development for the treatment thereof.

Hypertension occurs when the body's smaller blood vessels (arterioles)constrict, causing an increase in blood pressure. Because the bloodvessels constrict, the heart must work harder to maintain blood flow atthe higher pressures. Although the body may tolerate short periods ofincreased blood pressure, sustained hypertension may eventually resultin damage to multiple body organs, including the kidneys, brain, eyesand other tissues, causing a variety of maladies associated therewith.The elevated blood pressure may also damage the lining of the bloodvessels, accelerating the process of atherosclerosis and increasing thelikelihood that a blood clot may develop. This could lead to a heartattack and/or stroke. Sustained high blood pressure may eventuallyresult in an enlarged and damaged heart (hypertrophy), which may lead toheart failure.

Heart failure is the final common expression of a variety ofcardiovascular disorders, including ischemic heart disease. It ischaracterized by an inability of the heart to pump enough blood to meetthe body's needs and results in fatigue, reduced exercise capacity andpoor survival. It is estimated that approximately 5,000,000 people inthe United States suffer from heart failure, directly leading to 39,000deaths per year and contributing to another 225,000 deaths per year. Itis also estimated that greater than 400,000 new cases of heart failureare diagnosed each year. Heart failure accounts for over 900,000hospital admissions annually, and is the most common discharge diagnosisin patients over the age of 65 years. It has been reported that the costof treating heart failure in the United States exceeds $20 billionannually. Accordingly, heart failure is also a serious health problemdemanding significant research and development for the treatment and/ormanagement thereof.

Heart failure results in the activation of a number of body systems tocompensate for the heart's inability to pump sufficient blood. Many ofthese responses are mediated by an increase in the level of activationof the sympathetic nervous system, as well as by activation of multipleother neurohormonal responses. Generally speaking, this sympatheticnervous system activation signals the heart to increase heart rate andforce of contraction to increase the cardiac output; it signals thekidneys to expand the blood volume by retaining sodium and water; and itsignals the arterioles to constrict to elevate the blood pressure. Thecardiac, renal and vascular responses increase the workload of theheart, further accelerating myocardial damage and exacerbating the heartfailure state. Accordingly, it is desirable to reduce the level ofsympathetic nervous system activation in order to stop or at leastminimize this vicious cycle and thereby treat or manage the heartfailure.

A number of drug treatments have been proposed for the management ofhypertension, heart failure and other cardiovascular disorders. Theseinclude vasodilators to reduce the blood pressure and ease the workloadof the heart, diuretics to reduce fluid overload, inhibitors andblocking agents of the body's neurohormonal responses, and othermedicaments.

Various surgical procedures have also been proposed for these maladies.For example, heart transplantation has been proposed for patients whosuffer from severe, refractory heart failure. Alternatively, animplantable medical device such as a ventricular assist device (VAD) maybe implanted in the chest to increase the pumping action of the heart.Alternatively, an intra-aortic balloon pump (IABP) may be used formaintaining heart function for short periods of time, but typically nolonger than one month. Other surgical procedures are available as well.

It has been known for decades that the wall of the carotid sinus, astructure at the bifurcation of the common carotid arteries, containsstretch receptors (baroreceptors) that are sensitive to the bloodpressure. These receptors send signals via the carotid sinus nerve tothe brain, which in turn regulates the cardiovascular system to maintainnormal blood pressure (the baroreflex), in part through activation ofthe sympathetic nervous system. Electrical stimulation of the carotidsinus nerve (baropacing) has previously been proposed to reduce bloodpressure and the workload of the heart in the treatment of high bloodpressure and angina. For example, U.S. Pat. No. 6,073,048 to Kieval etal. discloses a baroreflex modulation system and method for stimulatingthe baroreflex arc based on various cardiovascular and pulmonaryparameters.

Although each of these alternative approaches is beneficial in someways, each of the therapies has its own disadvantages. For example, drugtherapy is often incompletely effective. Some patients may beunresponsive (refractory) to medical therapy. Drugs often have unwantedside effects and may need to be given in complex regimens. These andother factors contribute to poor patient compliance with medicaltherapy. Drug therapy may also be expensive, adding to the health carecosts associated with these disorders. Likewise, surgical approaches arevery costly, may be associated with significant patient morbidity andmortality and may not alter the natural history of the disease.Baropacing also has not gained acceptance. Several problems withelectrical carotid sinus nerve stimulation have been reported in themedical literature. These include the invasiveness of the surgicalprocedure to implant the nerve electrodes, and postoperative pain in thejaw, throat, face and head during stimulation. In addition, it has beennoted that high voltages sometimes required for nerve stimulation maydamage the carotid sinus nerves. Accordingly, there continues to be asubstantial and long felt need for new devices and methods for treatingand/or managing high blood pressure, heart failure and their associatedcardiovascular and nervous system disorders.

U.S. Pat. No. 6,522,926, signed to the Assignee of the presentapplication, describes a number of systems and methods intended toactivate baroreceptors in the carotid sinus and elsewhere in order toinduce the baroreflex. Numerous specific approaches are described,including the use of coil electrodes placed over the exterior of thecarotid sinus near the carotid bifurcation. While such electrode designsoffer substantial promise, there is room for improvement in a number ofspecific design areas. For example, it would be desirable to providedesigns which permit electrode structures to be closely and conformablysecured over the exterior of a carotid sinus or other blood vessels sothat efficient activation of the underlying baroreceptors can beachieved. It would be further desirable to provide specific electrodestructures which can be variably positioned at different locations overthe carotid sinus wall or elsewhere. At least some of these objectiveswill be met by these inventions described hereinbelow.

BRIEF SUMMARY OF THE INVENTION

To address hypertension, heart failure and their associatedcardiovascular and nervous system disorders, the present inventionprovides a number of devices, systems and methods by which the bloodpressure, nervous system activity, and neurohormonal activity may beselectively and controllably regulated by activating baroreceptors. Byselectively and controllably activating baroreceptors, the presentinvention reduces excessive blood pressure, sympathetic nervous systemactivation and neurohormonal activation, thereby minimizing theirdeleterious effects on the heart, vasculature and other organs andtissues.

The present invention provides systems and methods for treating apatient by inducing a baroreceptor signal to effect a change in thebaroreflex system (e.g., reduced heart rate, reduced blood pressure,etc.). The baroreceptor signal is activated or otherwise modified byselectively activating baroreceptors. To accomplish this, the system andmethod of the present invention utilize a baroreceptor activation devicepositioned near a baroreceptor in the carotid sinus, aortic arch, heart,common carotid arteries, subclavian arteries, and/or brachiocephalicartery. Preferably, the baroreceptor activation device is located in theright and/or left carotid sinus (near the bifurcation of the commoncarotid artery) and/or the aortic arch. By way of example, notlimitation, the present invention is described with reference to thecarotid sinus location.

Generally speaking, the baroreceptor activation device may be activated,deactivated or otherwise modulated to activate one or more baroreceptorsand induce a baroreceptor signal or a change in the baroreceptor signalto thereby effect a change in the baroreflex system. The baroreceptoractivation device may be activated, deactivated, or otherwise modulatedcontinuously, periodically, or episodically. The baroreceptor activationdevice may comprise a wide variety of devices which utilize electrodesto directly or indirectly activate the baroreceptor. The baroreceptormay be activated directly, or activated indirectly via the adjacentvascular tissue. The baroreceptor activation device will be positionedoutside the vascular wall. To maximize therapeutic efficacy, mappingmethods may be employed to precisely locate or position the baroreceptoractivation device.

The present invention is directed particularly at electrical means andmethods to activate baroreceptors, and various electrode designs areprovided. The electrode designs may be particularly suitable forconnection to the carotid arteries at or near the carotid sinus, and maybe designed to minimize extraneous tissue stimulation. While beingparticularly suitable for use on the carotid arteries at or near thecarotid sinus, the electrode structures and assemblies of the presentinvention will also find use for external placement and securement ofelectrodes about other arteries, and in some cases veins, havingbaroreceptor and other electrically activated receptors therein.

In a first aspect of the present invention, a baroreceptor activationdevice or other electrode useful for a carotid sinus or other bloodvessel comprises a base having one or more electrodes connected to thebase. The base has a length sufficient to extend around at least asubstantial portion of the circumference of a blood vessel, usually anartery, more usually a carotid artery at or near the carotid sinus. By“substantial portion,” it is meant that the base will extend over atleast 25% of the vessel circumference, usually at least 50%, moreusually at least 66%, and often at least 75% or over the entirecircumference. Usually, the base is sufficiently elastic to conform tosaid circumference or portion thereof when placed therearound. Theelectrode connected to the base is oriented at least partly in thecircumferential direction and is sufficiently stretchable to bothconform to the shape of the carotid sinus when the base is conformedthereover and accommodate changes in the shape and size of the sinus asthey vary over time with heart pulse and other factors, including bodymovement which causes the blood vessel circumference to change.

Usually, at least two electrodes will be positioned circumferentiallyand adjacent to each other on the base. The electrode(s) may extend overthe entire length of the base, but in some cases will extend over lessthan 75% of the circumferential length of the base, often being lessthan 50% of the circumferential length, and sometimes less than 25% ofthe circumferential length. Thus, the electrode structures may coverfrom a small portion up to the entire circumferential length of thecarotid artery or other blood vessel. Usually, the circumferentiallength of the elongate electrodes will cover at least 10% of thecircumference of the blood vessel, typically being at least 25%, oftenat least 50%, 75%, or the entire length. The base will usually havefirst and second ends, wherein the ends are adapted to be joined, andwill have sufficient structural integrity to grasp the carotid sinus.

In a further aspect of the present invention, an extravascular electrodeassembly comprises an elastic base and a stretchable electrode. Theelastic base is adapted to be conformably attached over the outside of atarget blood vessel, such as a carotid artery at or near the carotidsinus, and the stretchable electrode is secured over the elastic baseand capable of expanding and contracting together with the base. In thisway, the electrode assembly is conformable to the exterior of thecarotid sinus or other blood vessel. Preferably, the elastic base isplanar, typically comprising an elastomeric sheet. While the sheet maybe reinforced, the reinforcement will be arranged so that the sheetremains elastic and stretchable, at least in the circumferentialdirection, so that the base and electrode assembly may be placed andconformed over the exterior of the blood vessel. Suitable elastomericsheets may be composed of silicone, latex, and the like.

To assist in mounting the extravascular electrode over the carotid sinusor other blood vessel, the assembly will usually include two or moreattachment tabs extending from the elastomeric sheet at locations whichallow the tabs to overlap the elastic base and/or be directly attachedto the blood vessel wall when the base is wrapped around or otherwisesecured over a blood vessel. In this way, the tabs may be fastened tosecure the backing over the blood vessel.

Preferred stretchable electrodes comprise elongated coils, where thecoils may stretch and shorten in a spring-like manner. In particularlypreferred embodiments, the elongated coils will be flattened over atleast a portion of their lengths, where the flattened portion isoriented in parallel to the elastic base. The flattened coil providesimproved electrical contact when placed against the exterior of thecarotid sinus or other blood vessel.

In a further aspect of the present invention, an extravascular electrodeassembly comprises a base and an electrode structure. The base isadapted to be attached over the outside of a carotid artery or otherblood vessel and has an electrode-carrying surface formed over at leasta portion thereof. A plurality of attachment tabs extend away from theelectrode-carrying surface, where the tabs are arranged to permitselective ones thereof to be wrapped around a blood vessel while othersof the tabs may be selectively removed. The electrode structure on orover the electrode-carrying surface.

In preferred embodiments, the base includes at least one tab whichextends longitudinally from the electrode-carrying surface and at leasttwo tabs which extend away from the surface at opposite, transverseangles. In an even more preferred embodiment, the electrode-carryingsurface is rectangular, and at least two longitudinally extending tabsextend from adjacent corners of the rectangular surface. The twotransversely angled tabs extend at a transverse angle away from the sametwo corners.

As with prior embodiments, the electrode structure preferably includesone or more stretchable electrodes secured to the electrode-carryingsurface. The stretchable electrodes are preferably elongated coils, morepreferably being “flattened coils” to enhance electrical contact withthe blood vessel to be treated. The base is preferably an elastic base,more preferably being formed from an elastomeric sheet. The phrase“flattened coil,” as used herein, refers to an elongate electrodestructure including a plurality of successive turns where thecross-sectional profile is non-circular and which includes at least onegenerally flat or minimally curved face. Such coils may be formed byphysically deforming (flattening) a circular coil, e.g., as shown inFIG. 24 described below. Usually, the flattened coils will have across-section that has a width in the plane of the electrode assemblygreater than its height normal to the electrode assembly plane.Alternatively, the coils may be initially fabricated in the desiredgeometry having one generally flat (or minimally curved) face forcontacting tissue. Fully flattened coils, e.g., those having planarserpentine configurations, may also find use, but usually it will bepreferred to retain at least some thickness in the direction normal tothe flat or minimally curved tissue-contacting surface. Such thicknesshelps the coiled electrode protrude from the base and provide improvedtissue contact over the entire flattened surface.

In a still further aspect of the present invention, a method forwrapping an electrode assembly over a blood vessel comprises providingan electrode assembly having an elastic base and one or more stretchableelectrodes. The base is conformed over an exterior of the blood vessel,such as a carotid artery, and at least a portion of an electrode isstretched along with the base. Ends of the elastic base are securedtogether to hold the electrode assembly in place, typically with boththe elastic backing and stretchable electrode remaining under at leastslight tension to promote conformance to the vessel exterior. Theelectrode assembly will be located over a target site in the bloodvessel, typically a target site having an electrically activatedreceptor. Advantageously, the electrode structures of the presentinvention when wrapped under tension will flex and stretch withexpansions and contractions of the blood vessel. A presently preferredtarget site is a baroreceptor, particularly baroreceptors in or near thecarotid sinus.

In a still further aspect of the present invention, a method forwrapping an electrode assembly over a blood vessel comprises providingan electrode assembly including a base having an electrode-carryingsurface and an electrode structure on the electrode-carrying surface.The base is wrapped over a blood vessel, and some but not all of aplurality of attachment tags on the base are secured over the bloodvessel. Usually, the tabs which are not used to secure an electrodeassembly will be removed, typically by cutting. Preferred target sitesare electrically activated receptors, usually baroreceptors, moreusually baroreceptors on the carotid sinus. The use of such electrodeassemblies having multiple attachment tabs is particularly beneficialwhen securing the electrode assembly on a carotid artery near thecarotid sinus. By using particular tabs, as described in more detailbelow, the active electrode area can be positioned at any of a varietyof locations on the common, internal, and/or external carotid arteries.

In another aspect, the present invention comprises pressure measuringassemblies including an elastic base adapted to be mounted on the outerwall of a blood vessel under circumferential tension. A strainmeasurement sensor is positioned on the base to measure strain resultingfrom circumferential expansion of the vessel due to a blood pressureincrease. Usually, the base will wrap about the entire circumference ofthe vessel, although only a portion of the base need be elastic.Alternatively, a smaller base may be stapled, glued, clipped orotherwise secured over a “patch” of the vessel wall to detect strainvariations over the underlying surface. Exemplary sensors include straingauges and micro machined sensors (MEMS).

In yet another aspect, electrode assemblies according to the presentinvention comprise a base and at least three parallel elongate electrodestructures secured over a surface of the base. The base is attachable toan outside surface of a blood vessel, such as a carotid artery,particularly a carotid artery near the carotid sinus, and has a lengthsufficient to extend around at least a substantial portion of thecircumference of the blood vessel, typically extending around at least25% of the circumference, usually extending around at least 50% of thecircumference, preferably extending at least 66% of the circumference,and often extending around at least 75% of or the entire circumferenceof the blood vessel. As with prior embodiments, the base will preferablybe elastic and composed of any of the materials set forth previously.

The at least three parallel elongate electrode structures willpreferably be aligned in the circumferential direction of the base,i.e., the axis or direction of the base which will be alignedcircumferentially over the blood vessel when the base is mounted on theblood vessel. The electrode structures will preferably be stretchable,typically being elongate coils, often being flattened elongate coils, asalso described previously.

At least an outer pair of the electrode structures will be electricallyisolated from an inner electrode structure, and the outer electrodestructures will preferably be arranged in a U-pattern in order tosurround the inner electrode structure. In this way, the outer pair ofelectrodes can be connected using a single conductor taken from thebase, and the outer electrode structures and inner electrode structuremay be connected to separate poles on a power supply in order to operatein the “pseudo” tripolar mode described hereinbelow.

To address low blood pressure and other conditions requiring bloodpressure augmentation, the present invention provides electrode designsand methods utilizing such electrodes by which the blood pressure may beselectively and controllably regulated by inhibiting or dampeningbaroreceptor signals. By selectively and controllably inhibiting ordampening baroreceptor signals, the present invention reduces conditionsassociated with low blood pressure.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic illustration of the upper torso of a human bodyshowing the major arteries and veins and associated anatomy.

FIG. 2A is a cross-sectional schematic illustration of the carotid sinusand baroreceptors within the vascular wall.

FIG. 2B is a schematic illustration of baroreceptors within the vascularwall and the baroreflex system.

FIG. 3 is a schematic illustration of a baroreceptor activation systemin accordance with the present invention.

FIGS. 4A and 4B are schematic illustrations of a baroreceptor activationdevice in the form of an implantable extraluminal conductive structurewhich electrically induces a baroreceptor signal in accordance with anembodiment of the present invention.

FIGS. 5A-5F are schematic illustrations of various possible arrangementsof electrodes around the carotid sinus for extravascular electricalactivation embodiments.

FIG. 6 is a schematic illustration of a serpentine shaped electrode forextravascular electrical activation embodiments.

FIG. 7 is a schematic illustration of a plurality of electrodes alignedorthogonal to the direction of wrapping around the carotid sinus forextravascular electrical activation embodiments.

FIGS. 8-11 are schematic illustrations of various multi-channelelectrodes for extravascular electrical activation embodiments.

FIG. 12 is a schematic illustration of an extravascular electricalactivation device including a tether and an anchor disposed about thecarotid sinus and common carotid artery.

FIG. 13 is a schematic illustration of an alternative extravascularelectrical activation device including a plurality of ribs and a spine.

FIG. 14 is a schematic illustration of an electrode assembly forextravascular electrical activation embodiments.

FIG. 15 is a schematic illustration of a fragment of an alternativecable for use with an electrode assembly such as shown in FIG. 14.

FIG. 16 illustrates a foil strain gauge for measuring expansion force ofa carotid artery or other blood vessel.

FIG. 17 illustrates a transducer which is adhesively connected to thewall of an artery.

FIG. 18 is a cross-sectional view of the transducer of FIG. 17.

FIG. 19 illustrates a first exemplary electrode assembly having anelastic base and plurality of attachment tabs.

FIG. 20 is a more detailed illustration of the electrode-carryingsurface of the electrode assembly of FIG. 19.

FIG. 21 is a detailed illustration of electrode coils which are presentin an elongate lead of the electrode assembly of FIG. 19.

FIG. 22 is a detailed view of the electrode-carrying surface of anelectrode assembly similar to that shown in FIG. 20, except that theelectrodes have been flattened.

FIG. 23 is a cross-sectional view of the electrode structure of FIG. 22.

FIG. 24 illustrates the transition between the flattened andnon-flattened regions of the electrode coil of the electrode assemblyFIG. 20.

FIG. 25 is a cross-sectional view taken along the line 25-25 of FIG. 24.

FIG. 26 is a cross-sectional view taken along the line 26-26 of FIG. 24.

FIG. 27 is an illustration of a further exemplary electrode assemblyconstructed in accordance with the principles of the present invention.

FIG. 28 illustrates the electrode assembly of FIG. 27 wrapped around thecommon carotid artery near the carotid bifurcation.

FIG. 29 illustrates the electrode assembly of FIG. 27 wrapped around theinternal carotid artery.

FIG. 30 is similar to FIG. 29, but with the carotid bifurcation having adifferent geometry.

DETAILED DESCRIPTION OF THE INVENTION

The following detailed description should be read with reference to thedrawings in which similar elements in different drawings are numberedthe same. The drawings, which are not necessarily to scale, depictillustrative embodiments and are not intended to limit the scope of theinvention.

To better understand the present invention, it may be useful to explainsome of the basic vascular anatomy associated with the cardiovascularsystem. Refer to FIG. 1 which is a schematic illustration of the uppertorso of a human body 10 showing some of the major arteries and veins ofthe cardiovascular system. The left ventricle of the heart 11 pumpsoxygenated blood up into the aortic arch 12. The right subclavian artery13, the right common carotid artery 14, the left common carotid artery15 and the left subclavian artery 16 branch off the aortic arch 12proximal of the descending thoracic aorta 17. Although relatively short,a distinct vascular segment referred to as the brachiocephalic artery 22connects the right subclavian artery 13 and the right common carotidartery 14 to the aortic arch 12. The right carotid artery 14 bifurcatesinto the right external carotid artery 18 and the right internal carotidartery 19 at the right carotid sinus 20. Although not shown for purposesof clarity only, the left carotid artery 15 similarly bifurcates intothe left external carotid artery and the left internal carotid artery atthe left carotid sinus.

From the aortic arch 12, oxygenated blood flows into the carotidarteries 18/19 and the subclavian arteries 13/16. From the carotidarteries 18/19, oxygenated blood circulates through the head andcerebral vasculature and oxygen depleted blood returns to the heart 11by way of the jugular veins, of which only the right internal jugularvein 21 is shown for sake of clarity. From the sub clavian arteries13/16, oxygenated blood circulates through the upper peripheralvasculature and oxygen depleted blood returns to the heart by way of thesubclavian veins, of which only the right subclavian vein 23 is shown,also for sake of clarity. The heart 11 pumps the oxygen depleted bloodthrough the pulmonary system where it is reoxygenated. The re-oxygenatedblood returns to the heart 11 which pumps the re-oxygenated blood intothe aortic arch as described above, and the cycle repeats.

Within the arterial walls of the aortic arch 12, common carotid arteries14/15 (near the right carotid sinus 20 and left carotid sinus),subclavian arteries 13/16 and brachiocephalic artery 22 there arebaroreceptors 30. For example, as best seen in FIG. 2A, baroreceptors 30reside within the vascular walls of the carotid sinus 20. Baroreceptors30 are a type of stretch receptor used by the body to sense bloodpressure. An increase in blood pressure causes the arterial wall tostretch, and a decrease in blood pressure causes the arterial wall toreturn to its original size. Such a cycle is repeated with each beat ofthe heart. Because baroreceptors 30 are located within the arterialwall, they are able to sense deformation of the adjacent tissue, whichis indicative of a change in blood pressure. The baroreceptors 30located in the right carotid sinus 20, the left carotid sinus and theaortic arch 12 play the most significant role in sensing blood pressurethat affects the baroreflex system 50, which is described in more detailwith reference to FIG. 2B.

Refer now to FIG. 2B, which shows a schematic illustration ofbaroreceptors 30 disposed in a generic vascular wall 40 and a schematicflow chart of the baroreflex system 50. Baroreceptors 30 are profuselydistributed within the arterial walls 40 of the major arteries discussedpreviously, and generally form an arbor 32. The baroreceptor arbor 32comprises a plurality of baroreceptors 30, each of which transmitsbaroreceptor signals to the brain 52 via nerve 38. The baroreceptors 30are so profusely distributed and arborized within the vascular wall 40that discrete baroreceptor arbors 32 are not readily discernable. Tothis end, those skilled in the art will appreciate that thebaroreceptors 30 shown in FIG. 2B are primarily schematic for purposesof illustration and discussion.

Baroreceptor signals are used to activate a number of body systems whichcollectively may be referred to as the baroreflex system 50.Baroreceptors 30 are connected to the brain 52 via the nervous system51. Thus, the brain 52 is able to detect changes in blood pressure,which is indicative of cardiac output. If cardiac output is insufficientto meet demand (i.e., the heart 11 is unable to pump sufficient blood),the baroreflex system 50 activates a number of body systems, includingthe heart 11, kidneys 53, vessels 54, and other organs/tissues. Suchactivation of the baroreflex system 50 generally corresponds to anincrease in neurohormonal activity. Specifically, the baroreflex system50 initiates a neurohormonal sequence that signals the heart 11 toincrease heart rate and increase contraction force in order to increasecardiac output, signals the kidneys 53 to increase blood volume byretaining sodium and water, and signals the vessels 54 to constrict toelevate blood pressure. The cardiac, renal and vascular responsesincrease blood pressure and cardiac output 55, and thus increase theworkload of the heart 11. In a patient with heart failure, this furtheraccelerates myocardial damage and exacerbates the heart failure state.

To address the problems of hypertension, heart failure, othercardiovascular disorders and renal disorders, the present inventionbasically provides a number of devices, systems and methods by which thebaroreflex system 50 is activated to reduce excessive blood pressure,autonomic nervous system activity and neurohormonal activation. Inparticular, the present invention provides a number of devices, systemsand methods by which baroreceptors 30 may be activated, therebyindicating an increase in blood pressure and signaling the brain 52 toreduce the body's blood pressure and level of sympathetic nervous systemand neurohormonal activation, and increase parasypathetic nervous systemactivation, thus having a beneficial effect on the cardiovascular systemand other body systems.

With reference to FIG. 3, the present invention generally provides asystem including a control system 60, a baroreceptor activation device70, and a sensor 80 (optional), which generally operate in the followingmanner. The sensor(s) 80 optionally senses and/or monitors a parameter(e.g., cardiovascular function) indicative of the need to modify thebaroreflex system and generates a signal indicative of the parameter.The control system 60 generates a control signal as a function of thereceived sensor signal. The control signal activates, deactivates orotherwise modulates the baroreceptor activation device 70. Typically,activation of the device 70 results in activation of the baroreceptors30. Alternatively, deactivation or modulation of the baroreceptoractivation device 70 may cause or modify activation of the baroreceptors30. The baroreceptor activation device 70 may comprise a wide variety ofdevices which utilize electrical means to activate baroreceptors 30.Thus, when the sensor 80 detects a parameter indicative of the need tomodify the baroreflex system activity (e.g., excessive blood pressure),the control system 60 generates a control signal to modulate (e.g.activate) the baroreceptor activation device 70 thereby inducing abaroreceptor 30 signal that is perceived by the brain 52 to be apparentexcessive blood pressure. When the sensor 80 detects a parameterindicative of normal body function (e.g., normal blood pressure), thecontrol system 60 generates a control signal to modulate (e.g.,deactivate) the baroreceptor activation device 70.

As mentioned previously, the baroreceptor activation device 70 maycomprise a wide variety of devices which utilize electrical means toactivate the baroreceptors 30. The baroreceptor activation device 70 ofthe present invention comprises an electrode structure which directlyactivates one or more baroreceptors 30 by changing the electricalpotential across the baroreceptors 30. It is possible that changing theelectrical potential across the tissue surrounding the baroreceptors 30may cause the surrounding tissue to stretch or otherwise deform, thusmechanically activating the baroreceptors 30, in which case thestretchable and elastic electrode structures of the present inventionmay provide significant advantages.

All of the specific embodiments of the electrode structures of thepresent invention are suitable for implantation, and are preferablyimplanted using a minimally invasive surgical approach. The baroreceptoractivation device 70 may be positioned anywhere baroreceptors 30 arepresent. Such potential implantation sites are numerous, such as theaortic arch 12, in the common carotid arteries 18/19 near the carotidsinus 20, in the subclavian arteries 13/16, in the brachiocephalicartery 22, or in other arterial or venous locations. The electrodestructures of the present invention will be implanted such that they arepositioned on or over a vascular structure immediately adjacent thebaroreceptors 30. Preferably, the electrode structure of thebaroreceptor activation device 70 is implanted near the right carotidsinus 20 and/or the left carotid sinus (near the bifurcation of thecommon carotid artery) and/or the aortic arch 12, where baroreceptors 30have a significant impact on the baroreflex system 50. For purposes ofillustration only, the present invention is described with reference tobaroreceptor activation device 70 positioned near the carotid sinus 20.

The optional sensor 80 is operably coupled to the control system 60 byelectric sensor cable or lead 82. The sensor 80 may comprise anysuitable device that measures or monitors a parameter indicative of theneed to modify the activity of the baroreflex system. For example, thesensor 80 may comprise a physiologic transducer or gauge that measuresECG, blood pressure (systolic, diastolic, average or pulse pressure),blood volumetric flow rate, blood flow velocity, blood pH, O2 or CO2content, mixed venous oxygen saturation (SVO2), vasoactivity, nerveactivity, tissue activity, body movement, activity levels, respiration,or composition. Examples of suitable transducers or gauges for thesensor 80 include ECG electrodes, a piezoelectric pressure transducer,an ultrasonic flow velocity transducer, an ultrasonic volumetric flowrate transducer, a thermodilution flow velocity transducer, a capacitivepressure transducer, a membrane pH electrode, an optical detector(SVO2), tissue impedance (electrical), or a strain gauge. Although onlyone sensor 80 is shown, multiple sensors 80 of the same or differenttype at the same or different locations may be utilized.

An example of an implantable blood pressure measurement device that maybe disposed about a blood vessel is disclosed in U.S. Pat. No. 6,106,477to Miesel et al., the entire disclosure of which is incorporated hereinby reference. An example of a subcutaneous ECG monitor is available fromMedtronic under the trade name REVEAL ILR and is disclosed in PCTPublication No. WO 98/02209, the entire disclosure of which isincorporated herein by reference. Other examples are disclosed in U.S.Pat. Nos. 5,987,352 and 5,331,966, the entire disclosures of which areincorporated herein by reference. Examples of devices and methods formeasuring absolute blood pressure utilizing an ambient pressurereference are disclosed in U.S. Pat. No. 5,810,735 to Halperin et al.,U.S. Pat. No. 5,904,708 to Goedeke, and PCT Publication No. WO 00/16686to Brockway et al., the entire disclosures of which are incorporatedherein by reference. The sensor 80 described herein may take the form ofany of these devices or other devices that generally serve the samepurpose.

The sensor 80 is preferably positioned in a chamber of the heart 11, orin/on a major artery such as the aortic arch 12, a common carotid artery14/15, a subclavian artery 13/16 or the brachiocephalic artery 22, suchthat the parameter of interest may be readily ascertained. The sensor 80may be disposed inside the body such as in or on an artery, a vein or anerve (e.g. vagus nerve), or disposed outside the body, depending on thetype of transducer or gauge utilized. The sensor 80 may be separate fromthe baroreceptor activation device 70 or combined therewith. Forpurposes of illustration only, the sensor 80 is shown positioned on theright subclavian artery 13.

By way of example, the control system 60 includes a control block 61comprising a processor 63 and a memory 62. Control system 60 isconnected to the sensor 80 by way of sensor cable 82. Control system 60is also connected to the baroreceptor activation device 70 by way ofelectric control cable 72. Thus, the control system 60 receives a sensorsignal from the sensor 80 by way of sensor cable 82, and transmits acontrol signal to the baroreceptor activation device 70 by way ofcontrol cable 72.

The system components 60/70/80 may be directly linked via cables 72/82or by indirect means such as RF signal transceivers, ultrasonictransceivers or galvanic couplings. Examples of such indirectinterconnection devices are disclosed in U.S. Pat. No. 4,987,897 toFunke and U.S. Pat. No. 5,113,859 to Funke, the entire disclosures ofwhich are incorporated herein by reference.

The memory 62 may contain data related to the sensor signal, the controlsignal, and/or values and commands provided by the input device 64. Thememory 62 may also include software containing one or more algorithmsdefining one or more functions or relationships between the controlsignal and the sensor signal. The algorithm may dictate activation ordeactivation control signals depending on the sensor signal or amathematical derivative thereof The algorithm may dictate an activationor deactivation control signal when the sensor signal falls below alower predetermined threshold value, rises above an upper predeterminedthreshold value or when the sensor signal indicates a specificphysiologic event. The algorithm may dynamically alter the thresholdvalue as determined by the sensor input values.

As mentioned previously, the baroreceptor activation device 70 activatesbaroreceptors 30 electrically, optionally in combination withmechanical, thermal, chemical, biological or other co-activation. Insome instances, the control system 60 includes a driver 66 to providethe desired power mode for the baroreceptor activation device 70. Forexample, the driver 66 may comprise a power amplifier or the like andthe cable 72 may comprise electrical lead(s). In other instances, thedriver 66 may not be necessary, particularly if the processor 63generates a sufficiently strong electrical signal for low levelelectrical actuation of the baroreceptor activation device 70.

The control system 60 may operate as a closed loop utilizing feedbackfrom the sensor 80, or other sensors, such as heart rate sensors whichmay be incorporated or the electrode assembly, or as an open looputilizing reprogramming commands received by input device 64. The closedloop operation of the control system 60 preferably utilizes somefeedback from the transducer 80, but may also operate in an open loopmode without feedback. Programming commands received by the input device64 may directly influence the control signal, the output activationparameters, or may alter the software and related algorithms containedin memory 62. The treating physician and/or patient may provide commandsto input device 64. Display 65 may be used to view the sensor signal,control signal and/or the software/data contained in memory 62.

The control signal generated by the control system 60 may be continuous,periodic, alternating, episodic or a combination thereof, as dictated byan algorithm contained in memory 62. Continuous control signals includea constant pulse, a constant train of pulses, a triggered pulse and atriggered train of pulses. Examples of periodic control signals includeeach of the continuous control signals described above which have adesignated start time (e.g., beginning of each period as designated byminutes, hours, or days in combinations of) and a designated duration(e.g., seconds, minutes, hours, or days in combinations of). Examples ofalternating control signals include each of the continuous controlsignals as described above which alternate between the right and leftoutput channels. Examples of episodic control signals include each ofthe continuous control signals described above which are triggered by anepisode (e.g., activation by the physician/patient, an increase/decreasein blood pressure above a certain threshold, heart rate above/belowcertain levels, etc.).

The stimulus regimen governed by the control system 60 may be selectedto promote long term efficacy. It is theorized that uninterrupted orotherwise unchanging activation of the baroreceptors 30 may result inthe baroreceptors and/or the baroreflex system becoming less responsiveover time, thereby diminishing the long term effectiveness of thetherapy. Therefore, the stimulus regimen maybe selected to activate,deactivate or otherwise modulate the baroreceptor activation device 70in such a way that therapeutic efficacy is maintained preferably foryears.

In addition to maintaining therapeutic efficacy over time, the stimulusregimens of the present invention may be selected reduce powerrequirement/consumption of the system 60. As will be described in moredetail hereinafter, the stimulus regimen may dictate that thebaroreceptor activation device 70 be initially activated at a relativelyhigher energy and/or power level, and subsequently activated at arelatively lower energy and/or power level. The first level attains thedesired initial therapeutic effect, and the second (lower) levelsustains the desired therapeutic effect long term. By reducing theenergy and/or power levels after the desired therapeutic effect isinitially attained, the energy required or consumed by the activationdevice 70 is also reduced long term. This may correlate into systemshaving greater longevity and/or reduced size (due to reductions in thesize of the power supply and associated components).

A first general approach for a stimulus regimen which promotes long termefficacy and reduces power requirements/consumption involves generatinga control signal to cause the baroreceptor activation device 70 to havea first output level of relatively higher energy and/or power, andsubsequently changing the control signal to cause the baroreceptoractivation device 70 to have a second output level of relatively lowerenergy and/or power. The first output level may be selected andmaintained for sufficient time to attain the desired initial effect(e.g., reduced heart rate and/or blood pressure), after which the outputlevel may be reduced to the second level for sufficient time to sustainthe desired effect for the desired period of time.

For example, if the first output level has a power and/or energy valueof X1, the second output level may have a power and/or energy value ofX2, wherein X2 is less than X1. In some instances, X2 may be equal tozero, such that the first level is “on” and the second level is “off”.It is recognized that power and energy refer to two differentparameters, and in some cases, a change in one of the parameters (poweror energy) may not correlate to the same or similar change in the otherparameter. In the present invention, it is contemplated that a change inone or both of the parameters may be suitable to obtain the desiredresult of promoting long term efficacy.

It is also contemplated that more than two levels may be used. Eachfurther level may increase the output energy or power to attain thedesired effect, or decrease the output energy or power to retain thedesired effect. For example, in some instances, it may be desirable tohave further reductions in the output level if the desired effect may besustained at lower power or energy levels. In other instances,particularly when the desired effect is diminishing or is otherwise notsustained, it may be desirable to increase the output level until thedesired effect is reestablished, and subsequently decrease the outputlevel to sustain the effect.

The transition from each level may be a step function (e.g., a singlestep or a series of steps), a gradual transition over a period of time,or a combination thereof. In addition, the signal levels may becontinuous, periodic, alternating, or episodic as discussed previously.

In electrical activation using a non modulated signal, the output (poweror energy) level of the baroreceptor activation device 70 may be changedby adjusting the output signal voltage level, current level and/orsignal duration. The output signal of the baroreceptor activation device70 may be, for example, constant current or constant voltage. Inelectrical activation embodiments using a modulated signal, wherein theoutput signal comprises, for example, a series of pulses, several pulsecharacteristics may be changed individually or in combination to changethe power or energy level of the output signal. Such pulsecharacteristics include, but are not limited to: pulse amplitude (PA),pulse frequency (PF), pulse width or duration (PW), pulse waveform(square, triangular, sinusoidal, etc.), pulse polarity (for bipolarelectrodes) and pulse phase (monophasic, biphasic).

In electrical activation wherein the output signal comprises a pulsetrain, several other signal characteristics may be changed in additionto the pulse characteristics described above, as described in copendingapplication Ser. No. 09/964,079, the full disclosure of which isincorporated herein by reference.

FIGS. 4A and 4B show schematic illustrations of a baroreceptoractivation device 300 in the form of an extravascular electricallyconductive structure or electrode 302. The electrode structure 302 maycomprise a coil, braid or other structure capable of surrounding thevascular wall. Alternatively, the electrode structure 302 may compriseone or more electrode patches distributed around the outside surface ofthe vascular wall. Because the electrode structure 302 is disposed onthe outside surface of the vascular wall, intravascular deliverytechniques may not be practical, but minimally invasive surgicaltechniques will suffice. The extravascular electrode structure 302 mayreceive electrical signals directly from the driver 66 of the controlsystem 60 by way of electrical lead 304, or indirectly by utilizing aninductor (not shown) as described in copending commonly assignedapplication Ser. No. 10/402,393 (Attorney Docket No. 21433-000420),filed on the same day as the present application, the full disclosure ofwhich is incorporated herein by reference.

Refer now to FIGS. 5A-5F which show schematic illustrations of variouspossible arrangements of electrodes around the carotid sinus 20 forextravascular electrical activation embodiments, such as baroreceptoractivation device 300 described with reference to FIGS. 4A and 4B. Theelectrode designs illustrated and described hereinafter may beparticularly suitable for connection to the carotid arteries at or nearthe carotid sinus, and may be designed to minimize extraneous tissuestimulation.

In FIGS. 5A-5F, the carotid arteries are shown, including the common 14,the external 18 and the internal 19 carotid arteries. The location ofthe carotid sinus 20 may be identified by a landmark bulge 21, which istypically located on the internal carotid artery 19 just distal of thebifurcation, or extends across the bifurcation from the common carotidartery 14 to the internal carotid artery 19.

The carotid sinus 20, and in particular the bulge 21 of the carotidsinus, may contain a relatively high density of baroreceptors 30 (notshown) in the vascular wall. For this reason, it may be desirable toposition the electrodes 302 of the activation device 300 on and/oraround the sinus bulge 21 to maximize baroreceptor responsiveness and tominimize extraneous tissue stimulation.

It should be understood that the device 300 and electrodes 302 aremerely schematic, and only a portion of which may be shown, for purposesof illustrating various positions of the electrodes 302 on and/or aroundthe carotid sinus 20 and the sinus bulge 21. In each of the embodimentsdescribed herein, the electrodes 302 may be monopolar, bipolar, ortripolar (anode-cathode-anode or cathode-anode-cathode sets). Specificextravascular electrode designs are described in more detailhereinafter.

In FIG. 5A, the electrodes 302 of the extravascular electricalactivation device 300 extend around a portion or the entirecircumference of the sinus 20 in a circular fashion. Often, it would bedesirable to reverse the illustrated electrode configuration in actualuse. In FIG. 5B, the electrodes 302 of the extravascular electricalactivation device 300 extend around a portion or the entirecircumference of the sinus 20 in a helical fashion. In the helicalarrangement shown in FIG. 5B, the electrodes 302 may wrap around thesinus 20 any number of times to establish the desired electrode 302contact and coverage. In the circular arrangement shown in FIG. 5A, asingle pair of electrodes 302 may wrap around the sinus 20, or aplurality of electrode pairs 302 may be wrapped around the sinus 20 asshown in FIG. 5C to establish more electrode 302 contact and coverage.

The plurality of electrode pairs 302 may extend from a point proximal ofthe sinus 20 or bulge 21, to a point distal of the sinus 20 or bulge 21to ensure activation of baroreceptors 30 throughout the sinus 20 region.The electrodes 302 may be connected to a single channel or multiplechannels as discussed in more detail hereinafter. The plurality ofelectrode pairs 302 may be selectively activated for purposes oftargeting a specific area of the sinus 20 to increase baroreceptorresponsiveness, or for purposes of reducing the exposure of tissue areasto activation to maintain baroreceptor responsiveness long term.

In FIG. 5D, the electrodes 302 extend around the entire circumference ofthe sinus 20 in a criss cross fashion. The criss cross arrangement ofthe electrodes 302 establishes contact with both the internal 19 andexternal 18 carotid arteries around the carotid sinus 20. Similarly, inFIG. 5E, the electrodes 302 extend around all or a portion of thecircumference of the sinus 20, including the internal 19 and external 18carotid arteries at the bifurcation, and in some instances the commoncarotid artery 14. In FIG. 5F, the electrodes 302 extend around all or aportion of the circumference of the sinus 20, including the internal 19and external 18 carotid arteries distal of the bifurcation. In FIGS. 5Eand 5F, the extravascular electrical activation devices 300 are shown toinclude a substrate or base structure 306 which may encapsulate andinsulate the electrodes 302 and may provide a means for attachment tothe sinus 20 as described in more detail hereinafter.

From the foregoing discussion with reference to FIGS. 5A-5F, it shouldbe apparent that there are a number of suitable arrangements for theelectrodes 302 of the activation device 300, relative to the carotidsinus 20 and associated anatomy. In each of the examples given above,the electrodes 302 are wrapped around a portion of the carotidstructure, which may require deformation of the electrodes 302 fromtheir relaxed geometry (e.g., straight). To reduce or eliminate suchdeformation, the electrodes 302 and/or the base structure 306 may have arelaxed geometry that substantially conforms to the shape of the carotidanatomy at the point of attachment. In other words, the electrodes 302and the base structure or backing 306 may be pre shaped to conform tothe carotid anatomy in a substantially relaxed state. Alternatively, theelectrodes 302 may have a geometry and/or orientation that reduces theamount of electrode 302 strain. Optionally, as described in more detailbelow, the backing or base structure 306 may be elastic or stretchableto facilitate wrapping of and conforming to the carotid sinus or othervascular structure.

For example, in FIG. 6, the electrodes 302 are shown to have aserpentine or wavy shape. The serpentine shape of the electrodes 302reduces the amount of strain seen by the electrode material when wrappedaround a carotid structure. In addition, the serpentine shape of theelectrodes increases the contact surface area of the electrode 302 withthe carotid tissue. As an alternative, the electrodes 302 may bearranged to be substantially orthogonal to the wrap direction (i.e.,substantially parallel to the axis of the carotid arteries) as shown inFIG. 7. In this alternative, the electrodes 302 each have a length and awidth or diameter, wherein the length is substantially greater than thewidth or diameter. The electrodes 302 each have a longitudinal axisparallel to the length thereof, wherein the longitudinal axis isorthogonal to the wrap direction and substantially parallel to thelongitudinal axis of the carotid artery about which the device 300 iswrapped. As with the multiple electrode embodiments describedpreviously, the electrodes 302 may be connected to a single channel ormultiple channels as discussed in more detail hereinafter.

Refer now to FIGS. 8-11 which schematically illustrate variousmulti-channel electrodes for the extravascular electrical activationdevice 300. FIG. 8 illustrates a six (6) channel electrode assemblyincluding six (6) separate elongate electrodes 302 extending adjacent toand parallel with each other. The electrodes 302 are each connected tomulti-channel cable 304. Some of the electrodes 302 may be common,thereby reducing the number of conductors necessary in the cable 304.

Base structure or substrate 306 may comprise a flexible and electricallyinsulating material suitable for implantation, such as silicone, perhapsreinforced with a flexible material such as polyester fabric. The base306 may have a length suitable to wrap around all (360.degree.) or aportion (i.e., less than 360.degree.) of the circumference of one ormore of the carotid arteries adjacent the carotid sinus 20. Theelectrodes 302 may extend around a portion (i.e., less than 360.degree.such as 270.degree., 180.degree. or 90.degree.) of the circumference ofone or more of the carotid arteries adjacent the carotid sinus 20. Tothis end, the electrodes 302 may have a length that is less than (e.g.,75%, 50% or 25%) the length of the base 206. The electrodes 302 may beparallel, orthogonal or oblique to the length of the base 306, which isgenerally orthogonal to the axis of the carotid artery to which it isdisposed about. Preferably, the base structure or backing will beelastic (i.e., stretchable), typically being composed of at least inpart of silicone, latex, or other elastomer. If such elastic structuresare reinforced, the reinforcement should be arranged so that it does notinterfere with the ability of the base to stretch and conform to thevascular surface.

The electrodes 302 may comprise round wire, rectangular ribbon or foilformed of an electrically conductive and radiopaque material such asplatinum. The base structure 306 substantially encapsulates theelectrodes 302, leaving only an exposed area for electrical connectionto extravascular carotid sinus tissue. For example, each electrode 302may be partially recessed in the base 206 and may have one side exposedalong all or a portion of its length for electrical connection tocarotid tissue. Electrical paths through the carotid tissues may bedefined by one or more pairs of the elongate electrodes 302.

In all embodiments described with reference to FIGS. 8-11, themulti-channel electrodes 302 may be selectively activated for purposesof mapping and targeting a specific area of the carotid sinus 20 todetermine the best combination of electrodes 302 (e.g., individual pair,or groups of pairs) to activate for maximum baroreceptor responsiveness,as described elsewhere herein. In addition, the multi-channel electrodes302 may be selectively activated for purposes of reducing the exposureof tissue areas to activation to maintain long term efficacy asdescribed, as described elsewhere herein. For these purposes, it may beuseful to utilize more than two (2) electrode channels. Alternatively,the electrodes 302 may be connected to a single channel wherebybaroreceptors are uniformly activated throughout the sinus 20 region.

An alternative multi-channel electrode design is illustrated in FIG. 9.In this embodiment, the device 300 includes sixteen (16) individualelectrode pads 302 connected to 16 channel cable 304 via 4 channelconnectors 303. In this embodiment, the circular electrode pads 302 arepartially encapsulated by the base structure 306 to leave one face ofeach button electrode 302 exposed for electrical connection to carotidtissues. With this arrangement, electrical paths through the carotidtissues may be defined by one or more pairs (bipolar) or groups(tripolar) of electrode pads 302.

A variation of the multi-channel pad type electrode design isillustrated in FIG. 10. In this embodiment, the device 300 includessixteen (16) individual circular pad electrodes 302 surrounded bysixteen (16) rings 305, which collectively may be referred to asconcentric electrode pads 302/305. Pad electrodes 302 are connected to17 channel cable 304 via 4 channel connectors 303, and rings 305 arecommonly connected to 17 channel cable 304 via a single channelconnector 307. In this embodiment, the circular shaped electrodes 302and the rings 305 are partially encapsulated by the base structure 306to leave one face of each pad electrode 302 and one side of each ring305 exposed for electrical connection to carotid tissues. As analternative, two rings 305 may surround each electrode 302, with therings 305 being commonly connected. With these arrangements, electricalpaths through the carotid tissues may be defined between one or more padelectrode 302/ring 305 sets to create localized electrical paths.

Another variation of the multi-channel pad electrode design isillustrated in FIG. 11. In this embodiment, the device 300 includes acontrol IC chip 310 connected to 3 channel cable 304. The control chip310 is also connected to sixteen (16) individual pad electrodes 302 via4 channel connectors 303. The control chip 310 permits the number ofchannels in cable 304 to be reduced by utilizing a coding system. Thecontrol system 60 sends a coded control signal which is received by chip310. The chip 310 converts the code and enables or disables selectedelectrode 302 pairs in accordance with the code.

For example, the control signal may comprise a pulse wave form, whereineach pulse includes a different code. The code for each pulse causes thechip 310 to enable one or more pairs of electrodes, and to disable theremaining electrodes. Thus, the pulse is only transmitted to the enabledelectrode pair(s) corresponding to the code sent with that pulse. Eachsubsequent pulse would have a different code than the preceding pulse,such that the chip 310 enables and disables a different set ofelectrodes 302 corresponding to the different code. Thus, virtually anynumber of electrode pairs may be selectively activated using controlchip 310, without the need for a separate channel in cable 304 for eachelectrode 302. By reducing the number of channels in cable 304, the sizeand cost thereof may be reduced.

Optionally, the IC chip 310 may be connected to feedback sensor 80,taking advantage of the same functions as described with reference toFIG. 3. In addition, one or more of the electrodes 302 may be used asfeedback sensors when not enabled for activation. For example, such afeedback sensor electrode may be used to measure or monitor electricalconduction in the vascular wall to provide data analogous to an ECG.Alternatively, such a feedback sensor electrode may be used to sense achange in impedance due to changes in blood volume during a pulsepressure to provide data indicative of heart rate, blood pressure, orother physiologic parameter.

Refer now to FIG. 12 which schematically illustrates an extravascularelectrical activation device 300 including a support collar or anchor312. In this embodiment, the activation device 300 is wrapped around theinternal carotid artery 19 at the carotid sinus 20, and the supportcollar 312 is wrapped around the common carotid artery 14. Theactivation device 300 is connected to the support collar 312 by cables304, which act as a loose tether. With this arrangement, the collar 312isolates the activation device from movements and forces transmitted bythe cables 304 proximal of the support collar, such as may beencountered by movement of the control system 60 and/or driver 66. As analternative to support collar 312, a strain relief (not shown) may beconnected to the base structure 306 of the activation device 300 at thejuncture between the cables 304 and the base 306. With either approach,the position of the device 300 relative to the carotid anatomy may bebetter maintained despite movements of other parts of the system.

In this embodiment, the base structure 306 of the activation device 300may comprise molded tube, a tubular extrusion, or a sheet of materialwrapped into a tube shape utilizing a suture flap 308 with sutures 309as shown. The base structure 306 may be formed of a flexible andbiocompatible material such as silicone, which may be reinforced with aflexible material such as polyester fabric available under the tradename DACRON® to form a composite structure. The inside diameter of thebase structure 306 may correspond to the outside diameter of the carotidartery at the location of implantation, for example 6 to 8 mm. The wallthickness of the base structure 306 may be very thin to maintainflexibility and a low profile, for example less than 1 mm. If the device300 is to be disposed about a sinus bulge 21, a correspondingly shapedbulge may be formed into the base structure for added support andassistance in positioning.

The electrodes 302 (shown in phantom) may comprise round wire,rectangular ribbon or foil, formed of an electrically conductive andradiopaque material such as platinum or platinum iridium. The electrodesmay be molded into the base structure 306 or adhesively connected to theinside diameter thereof, leaving a portion of the electrode exposed forelectrical connection to carotid tissues. The electrodes 302 mayencompass less than the entire inside circumference (e.g., 300.degree.)of the base structure 306 to avoid shorting. The electrodes 302 may haveany of the shapes and arrangements described previously. For example, asshown in FIG. 12, two rectangular ribbon electrodes 302 may be used,each having a width of 1 mm spaced 1.5 mm apart.

The support collar 312 may be formed similarly to base structure 306.For example, the support collar may comprise molded tube, a tubularextrusion, or a sheet of material wrapped into a tube shape utilizing asuture flap 315 with sutures 313 as shown. The support collar 312 may beformed of a flexible and biocompatible material such as silicone, whichmay be reinforced to form a composite structure. The cables 304 aresecured to the support collar 312, leaving slack in the cables 304between the support collar 312 and the activation device 300.

In all embodiments described herein, it may be desirable to secure theactivation device to the vascular wall using sutures or other fixationmeans. For example, sutures 311 may be used to maintain the position ofthe electrical activation device 300 relative to the carotid anatomy (orother vascular site containing baroreceptors). Such sutures 311 may beconnected to base structure 306, and pass through all or a portion ofthe vascular wall. For example, the sutures 311 may be threaded throughthe base structure 306, through the adventitia of the vascular wall, andtied. If the base structure 306 comprises a patch or otherwise partiallysurrounds the carotid anatomy, the corners and/or ends of the basestructure may be sutured, with additional sutures evenly distributedtherebetween. In order to minimize the propagation of a hole or a tearthrough the base structure 306, a reinforcement material such aspolyester fabric may be embedded in the silicone material. In additionto sutures, other fixation means may be employed such as staples or abiocompatible adhesive, for example.

Refer now to FIG. 13 which schematically illustrates an alternativeextravascular electrical activation device 300 including one or moreelectrode ribs 316 interconnected by spine 317. Optionally, a supportcollar 312 having one or more (non electrode) ribs 316 may be used toisolate the activation device 300 from movements and forces transmittedby the cables 304 proximal of the support collar 312.

The ribs 316 of the activation device 300 are sized to fit about thecarotid anatomy, such as the internal carotid artery 19 adjacent thecarotid sinus 20. Similarly, the ribs 316 of the support collar 312 maybe sized to fit about the carotid anatomy, such as the common carotidartery 14 proximal of the carotid sinus 20. The ribs 316 may beseparated, placed on a carotid artery, and closed thereabout to securethe device 300 to the carotid anatomy.

Each of the ribs 316 of the device 300 includes an electrode 302 on theinside surface thereof for electrical connection to carotid tissues. Theribs 316 provide insulating material around the electrodes 302, leavingonly an inside portion exposed to the vascular wall. The electrodes 302are coupled to the multi-channel cable 304 through spine 317. Spine 317also acts as a tether to ribs 316 of the support collar 312, which donot include electrodes since their function is to provide support. Themulti-channel electrode 302 functions discussed with reference to FIGS.8-11 are equally applicable to this embodiment.

The ends of the ribs 316 may be connected (e.g., sutured) after beingdisposed about a carotid artery, or may remain open as shown. If theends remain open, the ribs 316 may be formed of a relatively stiffmaterial to ensure a mechanical lock around the carotid artery. Forexample, the ribs 316 may be formed of polyethylene, polypropylene,PTFE, or other similar insulating and biocompatible material.Alternatively, the ribs 316 may be formed of a metal such as stainlesssteel or a nickel titanium alloy, as long as the metallic material waselectrically isolated from the electrodes 302. As a further alternative,the ribs 316 may comprise an insulating and biocompatible polymericmaterial with the structural integrity provided by metallic (e.g.,stainless steel, nickel titanium alloy, etc.) reinforcement. In thislatter alternative, the electrodes 302 may comprise the metallicreinforcement.

Refer now to FIG. 14 which schematically illustrates a specific exampleof an electrode assembly for an extravascular electrical activationdevice 300. In this specific example, the base structure 306 comprises asilicone sheet having a length of 5.0 inches, a thickness of 0.007inches, and a width of 0.312 inches. The electrodes 302 compriseplatinum ribbon having a length of 0.47 inches, a thickness of 0.0005inches, and a width of 0.040 inches. The electrodes 302 are adhesivelyconnected to one side of the silicone sheet 306.

The electrodes 302 are connected to a modified bipolar endocardialpacing lead, available under the trade name CONIFIX from Innomedica (nowBIOMEC Cardiovascular, Inc.), model number 501112. The proximal end ofthe cable 304 is connected to the control system 60 or driver 66 asdescribed previously. The pacing lead is modified by removing the pacingelectrode to form the cable body 304. The MP35 wires are extracted fromthe distal end thereof to form two coils 318 positioned side by sidehaving a diameter of about 0.020 inches. The coils 318 are then attachedto the electrodes utilizing 316 type stainless steel crimp terminalslaser welded to one end of the platinum electrodes 302. The distal endof the cable 304 and the connection between the coils 318 and the endsof the electrodes 302 are encapsulated by silicone.

The cable 304 illustrated in FIG. 14 comprises a coaxial type cableincluding two coaxially disposed coil leads separated into two separatecoils 318 for attachment to the electrodes 302. An alternative cable 304construction is illustrated in FIG. 15. FIG. 15 illustrates analternative cable body 304 which may be formed in a curvilinear shapesuch as a sinusoidal configuration, prior to implantation. Thecurvilinear configuration readily accommodates a change in distancebetween the device 300 and the control system 60 or the driver 66. Sucha change in distance may be encountered during flexion and/or extensionof the neck of the patient after implantation.

In this alternative embodiment, the cable body 304 may comprise two ormore conductive wires 304 a arranged coaxially or collinearly as shown.Each conductive wire 304 a may comprise a multifilament structure ofsuitable conductive material such as stainless steel or MP35N. Aninsulating material may surround the wire conductors 304 a individuallyand/or collectively. For purposes of illustration only, a pair ofelectrically conductive wires 304 a having an insulating materialsurrounding each wire 304 a individually is shown. The insulated wires304 a may be connected by a spacer 304 b comprising, for example, aninsulating material. An additional jacket of suitable insulatingmaterial may surround each of the conductors 304 a. The insulatingjacket may be formed to have the same curvilinear shape of the insulatedwires 304 a to help maintain the shape of the cable body 304 duringimplantation.

If a sinusoidal configuration is chosen for the curvilinear shape, theamplitude (A) may range from 1 mm to 10 mm, and preferably ranges from 2mm to 3 mm. The wavelength (WL) of the sinusoid may range from 2 mm to20 mm, and preferably ranges from 4 mm to 10 mm. The curvilinear orsinusoidal shape may be formed by a heat setting procedure utilizing afixture which holds the cable 304 in the desired shape while the cableis exposed to heat. Sufficient heat is used to heat set the conductivewires 304 a and/or the surrounding insulating material. After cooling,the cable 304 may be removed from the fixture, and the cable 304 retainsthe desired shape.

Refer now to FIGS. 16-18 which illustrate various transducers that maybe mounted to the wall of a vessel such as a carotid artery 14 tomonitor wall expansion or contraction using strain, force and/orpressure gauges. An example of an implantable blood pressure measurementdevice that may be disposed about a blood vessel is disclosed in U.S.Pat. No. 6,106,477 to Miesel et al., the entire disclosure of which isincorporated herein by reference. The output from such gauges may becorrelated to blood pressure and/or heart rate, for example, and may beused to provide feedback to the control system 60 as describedpreviously herein. In FIG. 16, an implantable pressure measuringassembly comprises a foil strain gauge or force sensing resistor device740 disposed about an artery such as common carotid artery 14. Atransducer portion 742 may be mounted to a silicone base or backing 744which is wrapped around and sutured or otherwise attached to the artery14.

Alternatively, the transducer 750 may be adhesively connected to thewall of the artery 14 using a biologically compatible adhesive such ascyanoacrylate as shown in FIG. 17. In this embodiment, the transducer750 comprises a micro machined sensor (MEMS) that measures force orpressure. The MEMS transducer 750 includes a micro arm 752 (shown insection in FIG. 18) coupled to a silicon force sensor contained over anelastic base 754. A cap 756 covers the arm 752 a top portion of the base754. The base 754 include an interior opening creating access from thevessel wall 14 to the arm 752. An incompressible gel 756 fills the spacebetween the arm 752 and the vessel wall 14 such that force istransmitted to the arm upon expansion and contraction of the vesselwall. In both cases, changes in blood pressure within the artery causechanges in vessel wall stress which are detected by the transducer andwhich may be correlated with the blood pressure.

Refer now to FIGS. 19-21 which illustrate an alternative extravascularelectrical activation device 700, which, may also be referred to as anelectrode cuff device or more generally as an “electrode assembly.”Except as described herein and shown in the drawings, device 700 may bethe same in design and function as extravascular electrical activationdevice 300 described previously.

As seen in FIGS. 19 and 20, electrode assembly or cuff device 700includes coiled electrode conductors 702/704 embedded in a flexiblesupport 706. In the embodiment shown, an outer electrode coil 702 and aninner electrode coil 704 are used to provide a pseudo tripolararrangement, but other polar arrangements are applicable as well asdescribed previously. The coiled electrodes 702/704 may be formed offine round, flat or ellipsoidal wire such as 0.002 inch diameter roundPtIr alloy wire wound into a coil form having a nominal diameter of0.015 inches with a pitch of 0.004 inches, for example. The flexiblesupport or base 706 may be formed of a biocompatible and flexible(preferably elastic) material such as silicone or other suitable thinwalled elastomeric material having a wall thickness of 0.005 inches anda length (e.g., 2.95 inches) sufficient to surround the carotid sinus,for example.

Each turn of the coil in the contact area of the electrodes 702/704 isexposed from the flexible support 706 and any adhesive to form aconductive path to the artery wall. The exposed electrodes 702/704 mayhave a length (e.g., 0.236 inches) sufficient to extend around at leasta portion of the carotid sinus, for example. The electrode cuff 700 isassembled flat with the contact surfaces of the coil electrodes 702/704tangent to the inside plane of the flexible support 706. When theelectrode cuff 700 is wrapped around the artery, the inside contactsurfaces of the coiled electrodes 702/704 are naturally forced to extendslightly above the adjacent surface of the flexible support, therebyimproving contact to the artery wall.

The ratio of the diameter of the coiled electrodes 702/704 to the wirediameter is preferably large enough to allow the coil to bend andelongate without significant bending stress or torsional stress in thewire. Flexibility is a significant advantage of this design which allowsthe electrode cuff 700 to conform to the shape of the carotid artery andsinus, and permits expansion and contraction of the artery or sinuswithout encountering significant stress or fatigue. In particular, theflexible electrode cuff 700 may be wrapped around and stretched toconform to the shape of the carotid sinus and artery duringimplantation. This may be achieved without collapsing or distorting theshape of the artery and carotid sinus due to the compliance of theelectrode cuff 700. The flexible support 706 is able to flex and stretchwith the conductor coils 702/704 because of the absence of fabricreinforcement in the electrode contact portion of the cuff 700. Byconforming to the artery shape, and by the edge of the flexible support706 sealing against the artery wall, the amount of stray electricalfield and extraneous stimulation will likely be reduced.

The pitch of the coil electrodes 702/704 may be greater than the wirediameter in order to provide a space between each turn of the wire tothereby permit bending without necessarily requiring axial elongationthereof. For example, the pitch of the contact coils 702/704 may be0.004 inches per turn with a 0.002 inch diameter wire, which allows fora 0.002 inch space between the wires in each turn. The inside of thecoil may be filled with a flexible adhesive material such as siliconeadhesive which may fill the spaces between adjacent wire turns. Byfilling the small spaces between the adjacent coil turns, the chance ofpinching tissue between coil turns is minimized thereby avoidingabrasion to the artery wall. Thus, the embedded coil electrodes 702/704are mechanically captured and chemically bonded into the flexiblesupport 706. In the unlikely event that a coil electrode 702/704 comesloose from the support 706, the diameter of the coil is large enough tobe atraumatic to the artery wall. Preferably, the centerline of the coilelectrodes 702/704 lie near the neutral axis of electrode cuff structure700 and the flexible support 706 comprises a material with isotropicelasticity such as silicone in order to minimize the shear forces on theadhesive bonds between the coil electrodes 702/704 and the support 706.

The electrode coils 702/704 are connected to corresponding conductivecoils 712/714, respectively, in an elongate lead 710 which is connectedto the control system 60. Anchoring wings 718 may be provided on thelead 710 to tether the lead 710 to adjacent tissue and minimize theeffects or relative movement between the lead 710 and the electrode cuff700. As seen in FIG. 21, the conductive coils 712/714 may be formed of0.003 MP35N bifilar wires wound into 0.018 inch diameter coils which areelectrically connected to electrode coils 702/704 by splice wires 716.The conductive coils 712/714 may be individually covered by aninsulating covering 718 such as silicone tubing and collectively coveredby insulating covering 720.

The conductive material of the electrodes 702/704 may be a metal asdescribed above or a conductive polymer such as a silicone materialfilled with metallic particles such as Pt particles. In this latterembodiment, the polymeric electrodes may be integrally formed with theflexible support 706 with the electrode contacts comprising raised areason the inside surface of the flexible support 706 electrically coupledto the lead 710 by wires or wire coils. The use of polymeric electrodesmay be applied to other electrode design embodiments described elsewhereherein.

Reinforcement patches 708 such as DACRON® fabric may be selectivelyincorporated into the flexible support 706. For example, reinforcementpatches 708 may be incorporated into the ends or other areas of theflexible support 706 to accommodate suture anchors. The reinforcementpatches 708 provide points where the electrode cuff 700 may be suturedto the vessel wall and may also provide tissue in growth to furtheranchor the device 700 to the exterior of the vessel wall. For example,the fabric reinforcement patches 708 may extend beyond the edge of theflexible support 706 so that tissue in growth may help anchor theelectrode assembly or cuff 700 to the vessel wall and may reducereliance on the sutures to retain the electrode assembly 700 in place.As a substitute for or in addition to the sutures and tissue in growth,bioadhesives such as cyanoacrylate may be employed to secure the device700 to the vessel wall. In addition, an adhesive incorporatingconductive particles such as Pt coated micro spheres may be applied tothe exposed inside surfaces of the electrodes 702/704 to enhanceelectrical conduction to the tissue and possibly limit conduction alongone axis to limit extraneous tissue stimulation.

The reinforcement patches 708 may also be incorporated into the flexiblesupport 706 for strain relief purposes and to help retain the coils702/704 to the support 706 where the leads 710 attach to the electrodeassembly 700 as well as where the outer coil 702 loops back around theinner coil 704. Preferably, the patches 708 are selectively incorporatedinto the flexible support 706 to permit expansion and contraction of thedevice 700, particularly in the area of the electrodes 702/704. Inparticular, the flexible support 706 is only fabric reinforced inselected areas thereby maintaining the ability of the electrode cuff 700to stretch.

Referring now to FIGS. 22-26, the electrode assembly of FIGS. 19-21 canbe modified to have “flattened” coil electrodes in the region of theassembly where the electrodes contact the extravascular tissue. As shownin FIG. 22, an electrode-carrying surface 801 of the electrode assembly,is located generally between parallel reinforcement strips or tabs 808.The flattened coil section 810 will generally be exposed on a lowersurface 803 of the base 806 (FIG. 23) and will be covered orencapsulated by a parylene or other polymeric structure or material 802over an upper surface 805 thereof. The coil is formed with a generallycircular periphery 809, as best seen in FIGS. 24 and 26, and may bemechanically flattened, typically over a silicone or other supportinginsert 815, as best seen in FIG. 25. The use of the flattened coilstructure is particularly beneficial since it retains flexibility,allowing the electrodes to bend, stretch, and flex together with theelastomeric base 806, while also increasing the flat electrode areaavailable to contact the extravascular surface.

Referring now to FIGS. 27-30, an additional electrode assembly 900constructed in accordance with the principles of the present inventionwill be described. Electrode assembly 900 comprises an electrode base,typically an elastic base 902, typically formed from silicone or otherelastomeric material, having an electrode-carrying surface 904 and aplurality of attachment tabs 906 (906 a, 906 b, 906 c, and 906 d)extending from the electrode-carrying surface. The attachment tabs 906are preferably formed from the same material as the electrode-carryingsurface 904 of the base 902, but could be formed from other elastomericmaterials as well. In the latter case, the base will be molded,stretched or otherwise assembled from the various pieces. In theillustrated embodiment, the attachment tabs 906 are formed integrallywith the remainder of the base 902, i.e., typically being cut from asingle sheet of the elastomeric material.

The geometry of the electrode assembly 900, and in particular thegeometry of the base 902, is selected to permit a number of differentattachment modes to the blood vessel. In particular, the geometry of theassembly 902 of FIG. 27 is intended to permit attachment to variouslocations on the carotid arteries at or near the carotid sinus andcarotid bifurcation.

A number of reinforcement regions 910 (910 a, 910 b, 910 c, 910 d, and910 e) are attached to different locations on the base 902 to permitsuturing, clipping, stapling, or other fastening of the attachment tabs906 to each other and/or the electrode-carrying surface 904 of the base902. In the preferred embodiment intended for attachment at or aroundthe carotid sinus, a first reinforcement strip 910 a is provided over anend of the base 902 opposite to the end which carries the attachmenttabs. Pairs of reinforcement strips 910 b and 910 c are provided on eachof the axially aligned attachment tabs 906 a and 906 b, while similarpairs of reinforcement strips 910 d and 910 e are provided on each ofthe transversely angled attachment tabs 906 c and 906 d. In theillustrated embodiment, all attachment tabs will be provided on one sideof the base, preferably emanating from adjacent corners of therectangular electrode-carrying surface 904.

The structure of electrode assembly 900 permits the surgeon to implantthe electrode assembly so that the electrodes 920 (which are preferablystretchable, flat-coil electrodes as described in detail above), arelocated at a preferred location relative to the target baroreceptors.The preferred location may be determined, for example, as described incopending application Ser. No. 09/963,991, filed on Sep. 26, 2001, thefull disclosure of which incorporated herein by reference.

Once the preferred location for the electrodes 920 of the electrodeassembly 900 is determined, the surgeon may position the base 902 sothat the electrodes 920 are located appropriately relative to theunderlying baroreceptors. Thus, the electrodes 920 may be positionedover the common carotid artery CC as shown in FIG. 28, or over theinternal carotid artery IC, as shown in FIGS. 29 and 30. In FIG. 28, theassembly 900 may be attached by stretching the base 902 and attachmenttabs 906 a and 906 b over the exterior of the common carotid artery. Thereinforcement tabs 906 a or 906 b may then be secured to thereinforcement strip 910 a, either by suturing, stapling, fastening,gluing, welding, or other well-known means. Usually, the reinforcementtabs 906 c and 906 d will be cut off at their bases, as shown at 922 and924, respectively.

In other cases, the bulge of the carotid sinus and the baroreceptors maybe located differently with respect to the carotid bifurcation. Forexample, as shown in FIG. 29, the receptors may be located further upthe internal carotid artery IC so that the placement of electrodeassembly 900 as shown in FIG. 28 will not work. The assembly 900,however, may still be successfully attached by utilizing thetransversely angled attachment tabs 906 c and 906 d rather than thecentral or axial tabs 906 a and 906 b. As shown in FIG. 29, the lowertab 906 d is wrapped around the common carotid artery CC, while theupper attachment tab 906 c is wrapped around the internal carotid arteryIC. The axial attachment tabs 906 a and 906 b will usually be cut off(at locations 926), although neither of them could in some instancesalso be wrapped around the internal carotid artery IC. Again, the tabswhich are used may be stretched and attached to reinforcement strip 910a, as generally described above.

Referring to FIG. 30, in instances where the carotid bifurcation hasless of an angle, the assembly 900 may be attached using the upper axialattachment tab 906 a and be lower transversely angled attachment tab 906d. Attachment tabs 906 b and 906 c may be cut off, as shown at locations928 and 930, respectively. In all instances, the elastic nature of thebase 902 and the stretchable nature of the electrodes 920 permit thedesired conformance and secure mounting of the electrode assembly overthe carotid sinus. It would be appreciated that these or similarstructures would also be useful for mounting electrode structures atother locations in the vascular system.

In most activation device embodiments described herein, it may bedesirable to incorporate anti-inflammatory agents (e.g., steroid elutingelectrodes) such as described in U.S. Pat. No. 4,711,251 to Stokes, U.S.Pat. No. 5,522,874 to Gates and U.S. Pat. No. 4,972,848 to Di Domenicoet al., the entire disclosures of which are incorporated herein byreference. Such agents reduce tissue inflammation at the chronicinterface between the device (e.g., electrodes) and the vascular walltissue, to thereby increase the efficiency of stimulus transfer, reducepower consumption, and maintain activation efficiency, for example.

Those skilled in the art will recognize that the present invention maybe manifested in a variety of forms other than the specific embodimentsdescribed and contemplated herein. Accordingly, departures in form anddetail may be made without departing from the scope and spirit of thepresent invention as described in the appended claims.

1. An electrode assembly for an implantable medical device, comprising:a spine; and a plurality of electrodes protruding from the spine,wherein at least two electrodes protrude from the spine in opposingdirections and define a nerve-receiving channel; wherein, when saidelectrode assembly is not coupled to a nerve and said electrodes are ina relaxed state position, said nerve receiving channel comprises across-sectional area that is substantially less than a cross-sectionalarea of a nerve to which the electrode assembly is adapted to becoupled; and wherein, when coupled to said nerve, each electrode wrapsaround and directly contacts at least 60% of the circumference of thenerve.
 2. The electrode assembly of claim 1 wherein, when said electrodeassembly is not coupled to a nerve and said electrodes are in a relaxedstate position, the cross-sectional area of the nerve receiving channelis less than 80% of the cross-sectional area of the nerve.
 3. Theelectrode assembly of claim 2 wherein, when said electrode assembly isnot coupled to a nerve and said electrodes are in a relaxed stateposition, the cross-sectional area of the nerve receiving channel isless than 60% of the cross-sectional area of the nerve.
 4. The electrodeassembly of claim 1 wherein said plurality of electrodes comprises atleast three electrodes and at least two electrodes adjacent one anotheralong the spine protrude from the spine in a common direction.
 5. Theelectrode assembly of claim 1 wherein said spine includes a plurality ofelectrical conductors, and wherein each conductor is coupled to at leastone electrode, and is electrically insulated from all other of saidelectrical conductors.
 6. An implantable medical device, comprising: apulse generator; a lead assembly coupled to said pulse generator; and anelectrode assembly coupled to said lead assembly, wherein the electrodeassembly comprises a spine and a plurality of electrodes protruding fromthe spine, and wherein at least two electrodes protrude from the spinein opposing directions and define a nerve-receiving channel; wherein,when said electrode assembly is not coupled to a nerve and saidelectrodes are in a relaxed state position, said nerve receiving channelcomprises a cross-sectional area that is substantially less than across-sectional area of a nerve to which the electrode assembly isadapted to be coupled; and wherein, when coupled to said nerve, eachelectrode wraps around and directly contacts at least 70% of thecircumference of the nerve.
 7. The implantable medical device of claim 6wherein, when said electrode assembly is not coupled to a nerve and saidelectrodes are in a relaxed state position, the cross-sectional area ofthe nerve receiving channel is less than 80% of the cross-sectional areaof the nerve.
 8. The implantable medical device of claim 7 wherein, whensaid electrode assembly is not coupled to a nerve and said electrodesare in a relaxed state position, the cross-sectional area of the nervereceiving channel is less than 60% of the cross-sectional area of thenerve.
 9. The implantable medical device of claim 6 wherein saidplurality of electrodes comprises at least three electrodes and at leasttwo electrodes adjacent one another along the spine protrude from thespine in a common direction.
 10. The implantable medical device of claim6 wherein said spine includes a plurality of electrical conductors, andwherein each conductor is coupled to at least one electrode, and iselectrically insulated from all other of said electrical conductors. 11.An electrode assembly usable with an implantable medical device,comprising: a spine; and a plurality of curved fingers protruding fromsaid spine, wherein at least two fingers protrude from the spine inopposing directions and define a nerve-receiving channel, and wherein atleast one of said fingers comprises an electrode that is adapted toelectrically contact a nerve; wherein, when said electrode assembly isnot coupled to the nerve and said fingers are in a relaxed stateposition, said nerve-receiving channel comprises a cross-sectional areathat is substantially less than a cross-sectional area of a nerve towhich the electrode assembly is adapted to be coupled; and wherein, whencoupled to said nerve, all of said fingers contact the nerve on apartial outer surface of the nerve, said partial outer surface extendingcircumferentially at least approximately 40% of the circumference of thenerve.
 12. The electrode assembly of claim 11 wherein each finger wrapsaround and directly contacts at least 70% of the circumference of thenerve.
 13. The electrode assembly of claim 11 wherein at least twofingers comprise an electrode.
 14. The electrode assembly of claim 11wherein, when said electrode assembly is not coupled to a nerve and saidfingers are in a relaxed state position, the cross-sectional area of thenerve receiving channel is less than 80% of the cross-sectional area ofthe nerve.
 15. The electrode assembly of claim 14 wherein, when saidelectrode assembly is not coupled to a nerve and said fingers are in arelaxed state position, the cross-sectional area of the nerve receivingchannel is less than 60% of the cross-sectional area of the nerve. 16.An electrode assembly for an implantable medical device, comprising: aspine; and a plurality of electrodes protruding from the spine, whereinat least two electrodes protrude from the spine in opposing directionsand define a nerve-receiving channel; wherein, when said electrodeassembly is not coupled to a nerve and said electrodes are in a relaxedstate position, said nerve receiving channel comprises a cross-sectionalarea that is less than 80% of the cross-sectional area of a nerve towhich the electrode assembly is adapted to be coupled.